96-Well Plasmonic Sensing with Nanohole Arrays - ACS Sensors

Subscriber access provided by MAHIDOL UNIVERSITY (UniNet)

Article

96-Well Plasmonic Sensing with Nanohole Arrays Maxime Couture, Korak Kumar Ray, Hugo-Pierre Poirier-Richard, Anthony Crofton, and Jean-Francois Masson ACS Sens., Just Accepted Manuscript • DOI: 10.1021/acssensors.5b00280 • Publication Date (Web): 15 Jan 2016 Downloaded from http://pubs.acs.org on January 23, 2016

Just Accepted “Just Accepted” manuscripts have been peer-reviewed and accepted for publication. They are posted online prior to technical editing, formatting for publication and author proofing. The American Chemical Society provides “Just Accepted” as a free service to the research community to expedite the dissemination of scientific material as soon as possible after acceptance. “Just Accepted” manuscripts appear in full in PDF format accompanied by an HTML abstract. “Just Accepted” manuscripts have been fully peer reviewed, but should not be considered the official version of record. They are accessible to all readers and citable by the Digital Object Identifier (DOI®). “Just Accepted” is an optional service offered to authors. Therefore, the “Just Accepted” Web site may not include all articles that will be published in the journal. After a manuscript is technically edited and formatted, it will be removed from the “Just Accepted” Web site and published as an ASAP article. Note that technical editing may introduce minor changes to the manuscript text and/or graphics which could affect content, and all legal disclaimers and ethical guidelines that apply to the journal pertain. ACS cannot be held responsible for errors or consequences arising from the use of information contained in these “Just Accepted” manuscripts.

ACS Sensors is published by the American Chemical Society. 1155 Sixteenth Street N.W., Washington, DC 20036 Published by American Chemical Society. Copyright © American Chemical Society. However, no copyright claim is made to original U.S. Government works, or works produced by employees of any Commonwealth realm Crown government in the course of their duties.

Page 1 of 17

1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60

ACS Sensors

96-Well Plasmonic Sensing with Nanohole Arrays Maxime Couture 1, Korak Kumar Ray 1, Hugo-Pierre Poirier-Richard 1, Anthony Crofton and Jean-Francois Masson* 1,2

1

1

Département de chimie, Université de Montréal, CP. 6128 Succ. Centre-Ville, Montréal, Qc,

Canada, H3C 3J7 2

Centre for self-assembled chemical structures (CSACS)

* Corresponding author: [email protected] ; tel : +1-514-343-7342

Abstract

A multi-well plasmonic reader was designed and validated for higher throughput analysis of biological interactions with a platform of the same size as standard 96-well plates. While the plasmonic sensor can be read with standard 96-well plate readers, a custom 96-well plate reader was designed to analyze nanohole arrays at high incident angles required for higher sensitivity. Gold nanohole arrays were manufactured on a 4 inch glass wafer using a photolithographic process. In comparison to single channel measurements with nanohole arrays fabricated with nanosphere lithography, the nanohole array sensors greatly enhanced the signal to noise ratio of the plasmonic signal and precision of the measurements with the multi-well plate system. As proof of concept, the detection of IgG in the low nanomolar range was achieved with the multiwell plate reader. The multi-well plasmonic plate reader was also applied to the screening of several prostate specific (PSA) antibodies for secondary detection of PSA and for the analysis of an anti-cancer drug through a competitive assay between methotrexate (MTX) and folic acid Au nanoparticle (FaNP) for human dihydrofolate reductase (hDHFR). The multi-well plasmonic reader based on nanohole array technology offers the rapid, versatile, sensitive and simple high throughput detection of biomolecules. Keywords: Nanohole array, multi-well plate reader, high throughput, plasmonic sensing, multiplexing, PSA, methotrexate

ACS Paragon Plus Environment

1

ACS Sensors

1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60

Page 2 of 17

Plasmonic biosensors have been widely studied in the last decades in order to develop applications in biomedical, environmental and clinical fields1. The popularity of plasmonic devices is due to their high sensitivity, rapid response, label-free detection and real-time analysis of biological interactions2. Plasmonic structures support surface plasmons which can be excited through coupling of incident light with a prism, as with classical surface plasmon resonance (SPR), a diffraction grating or with resonances in nanoparticles or nanostructures resulting in localized surface plasmon resonance (LSPR)3. Plasmonic biosensors are sensitive towards refractive index variation, measuring binding events occurring on the surface of a sensor. Due to this refractive index sensitivity and thus the generality of the sensing principle, SPR sensors have been demonstrated for a series of biomarkers4-5, drugs6, DNA7, environmental contaminants8, among many other applications. SPR sensing is now the gold standard in academic research or industry for label-free optical biosensing 9. However, some concerns were expressed towards the future of SPR biosensors due to several limitations such as low throughput capabilities, difficult miniaturization and sensitivity1. Nowadays, commercial SPR systems offer multi-channel analysis in parallel for up to 16 channels. Despite this moderate throughput, conventional SPR systems are still lacking compared to 96 well-plate or higher throughput well-plate technologies based on an enzyme linked immunosorbent assay (ELISA)10. Higher throughput SPR sensing can be achieved with the imaging format of SPR. However, the fabrication of the sensor arrays is relatively complex and most applications reported to date with this technology had modest throughput, with n x n arrays in which n is often between 3 and 5. SPR in the imaging format also suffers from poorer refractive index resolution than the classical versions of SPR. SPR and ELISA share several key features. They are both relying on the interaction of the analyte with a surface-bound receptor. The applications accessible to SPR and ELISA overlaps significantly, especially for the analysis of proteins or molecules for which antibodies exists. Therefore, ELISA is the gold standard for evaluating the performances of SPR. The comparative studies of SPR and ELISA have demonstrated that both techniques benefit from similar analytical performances 11-13, such as detection limits, linearity and reproducibility on the same order of magnitude. Multi-well plate ELISAs remain the standard analytical tool in clinical analysis despite disadvantages such as being time and reagent consuming compared to SPR. Therefore, the development of an SPR-based technology benefitting from all the advantages of ELISA in the multi-well plate format could increase the throughput of SPR sensors for label-free analysis. Nanoplasmonic structures can provide benefits such as low-cost instrumentation, miniaturization, large-scale fabrication processes and high throughput capabilities. Sensing with nanoplasmonic structures is typically performed with transmission optical measurements and thus are compatible with multi-well plate readers and therefore nanoplasmonic biosensors are considered to be the next-generation of plasmonic sensing platforms1. Several nanoplasmonic structures have been developed for biosensing such as nanostructured arrays3-14. In the last decade, nanohole arrays have attracted significant interest due to their versatility and large domain of applications15-16. Ebbesen and coworkers have demonstrated that coupling of light with an array of holes with a diameter smaller than the incident wavelength generates extraordinary optical transmission (EOT) 17-18. Coupling of light with surface plasmon polaritons (SPPs) generate Bloch-Wave SPPs that are associated with different orders of diffraction of light19. The plasmonic properties and the wavelength of excitation of the plasmon resonance of nanohole


2

Page 3 of 17

1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60

ACS Sensors

arrays can be tuned with several structural parameters such as hole diameter and depth, periodicity, metallic composition and array orientation20. We recently demonstrated that the penetration depth of nanohole arrays can be decreased with higher incidence, which led to higher surface sensitivity with holes having a large diameter (~ 500-600 nm) and periodicity (~800-1000 nm) 21. A higher incidence angle also allowed the excitation of plasmonic modes in the visible region that would normally be excited in the NIR (at 0° in transmission) for array with a large periodicity. Thus, detection of protein was reported in low nM range with performances similar to SPR. Thereby, the gap is closing in the performance of nanohole arrays in comparison to SPR and thus, nanohole arrays are a highly relevant plasmonic structure that have a great potential for multiplexing analysis. In this paper, we demonstrate the multiplexing capabilities of gold nanohole arrays using a custom built multi-well plate reader. Nanohole arrays were manufactured by photolithography which generated highly uniform structures on a large scale. Commercial plate readers do not possess the ability to control the incidence angle of the light beam necessary for high sensitivity when using nanohole arrays and was thus included in the current plate reader design. The robot was coupled to a commercial spectrophotometer to scan a 96-well plate for plasmonic sensing. The performance and versatility of the system was assessed through the sensing of various biological interactions previously reported elsewhere, such as the detection of IgG in PBS buffer, screening of various antibodies for prostate specific antigen22 (PSA), and for the detection of methotrexate23 (MTX) in phosphate buffer.

Experimental section Nanohole array fabrication Gold nanohole arrays were manufactured according to photolithographic techniques. All the microfabrication steps were performed in a clean room of class 100. Glass BK7 wafers of 4’’ (UniversityWafer, Boston, MA) were cleaned by piranha solution (3:1 ratio of H2SO4:H2O2) for 20 minutes (Caution! piranha solution is highly corrosive). The glass wafers were rinsed thoroughly with ultrapure water and dried under a nitrogen stream. The clean wafers were then coated with 2 nm of chromium using electron beam deposition. This layer of chromium decreased back reflection effect during exposition. A negative photoresist (AZ nLOF 2020, Microchemicals, Ulm, Germany) was spin coated onto the glass wafer according to the manufacturer directives. The chromium mask (Photomask Portal, Richardson, TX) corresponded to an array of holes having a diameter of 720 nm and periodicity of 1200 nm. The spin-coated wafers were exposed with a dose of 88.7 mJ/seconds in I-line (365 nm) through the patterned mask using a MA6 aligner (SUSS Microtec, Garching, Germany) in vacuum mode. A post exposure bake was then performed at 115°C for 90 seconds. The wafers were developed in AZ 726 MIF for 3 minutes under constant agitation. Afterwards, 2 nm of Cr and 120 nm of gold were deposited on the patterned wafer using electron beam deposition. The array of pillars was lifted off from the wafer by sonication in remover PG. In order to fit in the multi-well plate, the patterned area of the wafer was cut using a 7100 Provectus dicing saw (Advanced Dicing Technology, Horsham, PA). Gold nanohole arrays with a periodicity of 1000 nm and diameter of 600 nm were fabricated by nanosphere lithography according to a previous report21. The structure of the nanohole arrays was confirmed by scanning electron microscopy (SEM, Jeol) and atomic force microscopy (AFM, Witec, Ulm, Germany).


3

ACS Sensors

1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60

Page 4 of 17

Instrumentation The multi-well plate reader was custom built in our research group. A multi-well plate holder stage was controlled in the X-Y plane using linear drives with a lateral movement and a precision of 0.25 mm. Stepper motors (part number: 16M4197) and linear guides (part number: 78T3143) were purchased from Newark element14 (Chicago, IL). The sample holder was designed to host a multi-well plate of standard size and was directly mounted on the X-Y stage. A raspberry Pi powered by a 5V power unit (PTN7800WAH, Texas Instruments) controlled the position of the plate and interface with the spectrophotometer. A custom printed system board was linked to the raspberry Pi and the stepper driver (DRV8811, Texas Instruments). The whole system is powered by a VGS-100-24 power supply (CUI) of 108W at 24V. The raspberry PI is configured as a server, which is linked via a TCP/IP connection to a computer. A Java/Swing code was used to design software allowing for control of the position of the multi-well plate upon action of the stepper motors via the raspberry Pi (Figure SI1). The software allows for the selection of wells to analyze, assign references, define number of sequences, vary acquisition parameters and observe signal in real-time. A mechanical arm allowed the excitation of the multi-well plate with an incident angle up to 50°. The sensors were excited with a broadband halogen source and the signal was collected with a PI-Acton spectrophotometer (Princeton) equipped with a grating of 650 g mm-1 (set from 584 to 716 nm) and a CCD camera (Andor model DU401A-BR-DD-152). Data was acquired by collecting an average of 10 spectra with an integration time of 100 ms per well. The 96-well plate was custom made of aluminium parts and a PDMS spacer was placed on the sensors to create the well and to avoid leaking between wells (Figure 3a). The position of the well and the overall dimension of the plate were identical to commercial 96-well plates (Figure SI2). However, the wells have an oval shape with a length of 7 mm and width of 3 mm, which allowed for the collection of higher signal intensity with incident angles. A top aluminum mount was used to compress the PDMS spacer on the sensors and maintain the assembly of the plate. A PMMA slide was used to cover the plate in order to eliminate a lensing effect from the solution inside the wells due to surface tension. The volume of the wells was controlled from the thickness of the PDMS spacer for a total volume of 90 µL. The solutions were delivered to the multi-well plate with an 8-channel pipette, however, robots designed for fluid handling with multi-well plates could also be used. The program used for data treatment was written in Python 3.4, using the tkinter module to implement the graphic user interface (GUI). The GUI consists of 96 buttons used to represent each well and a number of functions to plot and analyse the spectra from the wells selected (Figure SI3). The raw intensity spectrum was divided by the reference spectrum to cancel out artefacts from the light source. This spectrum was then fitted to a parabola. The derivative of the parabola was computed and its root was calculated to find the minimum of the curve. Because the spectrum was only parabolic in a certain region near the minimum, the range of the spectrum to be fitted to a parabola was manually inputted after inspection of the intensity plot. To avoid divergences in the calculated minima depending on the input of the calculation boundaries, the range was increased by adding 10 pixels at the end, and the minimum was again computed. If the new minimum differed from the previous one by a large amount (more than 0.1 nm), the program generated a warning that the range may not be the optimal one for the analysis.


4

Page 5 of 17

1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60

ACS Sensors

Plasmonic sensing For all sensors, the transmission minima shift, also termed plasmonic shift (∆λSP)corresponded to the difference between the measurement of the plasmonic response in buffer before and after the detection of the target. A measurement consisted of an average of 3 individual wells prepared identically. The measurements were acquired in a single-measurement mode rather than the realtime kinetics common to SPR instruments. The nanohole arrays were excited at an incident angle of 50° to maximize sensitivity and a typical plasmonic signal of the sensors is shown in Figure SI4. The stability of the plate was assessed with successive detection of water and PBS and a calibration curve of sucrose solutions was made for refractive index units (RI) of 1.33 to 1.37. For every biosensing analysis, a self-assembled monolayer (SAM) of 3-MPA-LHDLHD-OH peptide was formed on the sensors’ surface as described in previous reports24. The plasmonic signal was measured 3 times for each well during a sequence. A total of 3 sequences was done for each measurements steps, thus every sensors in the multi-well plate were scanned 9 times to measure repeatability. Between each sequence, the multi-well plate was removed and inserted back in the plate holder to measure the variation in response due to different alignments of the plate. The transmission signal of a 50 nm Au film was used as a reference for the normalization of the plasmonic signal. The thickness of this reference Au film has been selected to efficiently compensate the intensity profile of the light source, absorption and scattering of Au. Au films of an equivalent thickness to the nanohole arrays are opaque and cannot be used to compensate the light source, while thin Au films are not accurately compensating for the absorption and scattering properties of Au. IgG detection The materials and methods involving biosensing of IgG and secondary detection of PSA have been reported elsewhere and used without change in this study 13-20. A calibration curve was performed for IgG concentrations ranging from 10 to 1000 nM via secondary antibody detection to enhance the plasmonic shift. For every assay, multiple wells were used as controls and references to validate the results. Anti-PSA screening PSA antibodies (labelled 20-PR50, 70-XG69, 10-P21A and 10-20A by the manufacturer) and PSA protein were purchased from Fitzgerald (Acton, MA). For the antibody screening test, multiple combinations of surface and capture antibodies were tested for detection of 1 µM of PSA in PBS. For each assay, the concentration of both surface and capture anti-PSA injected in the wells was 75 µg/mL. The optimal anti-PSA pair (20-PR50 and 70-XG69) was used to perform a calibration curve of PSA for concentrations ranging from 1 to 1000 nM in PBS.

MTX monitoring The competitive detection of MTX in phosphate buffer (PB) using FaNP and hDHFR was performed as previously reported 23. MTX is a toxic compound and special care must be taken during its manipulation; wearing a protective mask is highly suggested. MTX was calibrated in


5

ACS Sensors

1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60

Page 6 of 17

the concentration range from 1 to 1000 nM in phosphate buffer, which coincides with the clinical range of interest.

Results and discussion Nanohole arrays Sub-wavelength nanohole arrays can be complex and expensive to manufacture in large areas due to the expensive and time-consuming microfabrication methodologies based on electron beam lithography14 or focus ion beam lithography25. Nanoimprinting lithography (NL) can also be used to achieve mass fabrication of uniform substrate on wafers 16-26, but is limited by availability and the somewhat expensive procedures for the fabrication of the moulds. In our group, we previously fabricated nanohole arrays by nanosphere lithography20-27, which is a low-cost, versatile and simple technique. However this is an imperfect process with several defects including areas missing nanostructures, different crystal orientations and other local defects which affect the optical properties of nanohole arrays. Structural uniformity is highly important with nanohole arrays to avoid any signal variation due to probing of different areas of the sensor. For these reasons, we adapted a microfabrication technique for nanohole arrays based on photolithography since it offers high uniformity (< 10% variation) and large area fabrication on 4’’ wafers. Photolithographic techniques are widely reported in the literature28 for microfabrication of semi-conductor integrated circuits due to its speed, large-scale fabrication and resolution. However, photolithography29 remains uncommon25 for the manufacture of plasmonic substrates on a glass wafer, due to the small size of the plasmonic features in most cases. In this study, the use of large periodicity Au nanohole arrays facilitated the use of photolithography for the fabrication of nanohole arrays. Large periodicities for nanohole arrays typically result in excitation of the plasmon in the near-infrared to infrared region, however the use of high incidence angles blue shifted the plasmon resonance to the visible to NIR region, suitable for the plate reader21. This photolithographic technique greatly improved the reproducibility of the fabrication process. However, we still experienced issues that limited the fabrication to around 70% of a glass wafer that could be covered with gold nanohole arrays (Figure 1a). The transparent areas observed on Figure 1a were due to Newton ring’s effect30, which is a common issue in photolithography, especially with glass wafer. Some of the issues reported here were due to the use of transparent glass wafers, in opposition to the common opaque Si wafers. However, glass wafers were necessary to transmit light in the EOT experiments reported in this manuscript. Among the challenges that were encountered in the fabrication process, the limit of resolution of the I-line (365 nm) of the MA6 mask aligner (~ 700 nm) and the scattered light effect31 due to the chuck’s aligner, were important. The optimal parameters for the nanohole arrays were a diameter of 720 nm and a periodicity of 1200 nm for a hexagonal array and thus the photomask mask was designed to expose features at the limit of resolution of the instrument. This was a compromise between the ease of the fabrication process and the excitation of the plasmon band near 700 nm at the maximum angle accessible using the plate reader. A vacuum contact was applied during exposition of the wafer to enhance the resolution31. Furthermore, the glass wafers were coated with a Cr layer of 2 nm to minimize back-reflections coming from the chuck, which overexposed the resin. The performance of the microfabrication process could be enhanced in the future with


6

Page 7 of 17

1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60

ACS Sensors

higher quality glass wafers, with a lower total thickness variation (TTV), which were not accessible to us at this stage. Overall, we obtained a plasmonic wafer with a very uniform structure (Figure 1b) and few local defects on a large surface. The plasmonic signal of nanohole arrays excited at 50° with the multi-well plate reader is shown at Figure 1c. Such structures offer an intense plasmonic signal near 650 nm with a FWHM of 50 nm.

Multi-well plate reader The multi-well plate reader was custom built to provide access to high excitation angles, unavailable on commercial plate readers. The system allowed for the analysis of a custom 96-well plate (figure 2a). A raspberry PI controlled the movement of the robot in the X-Y axis upon motion of the motor stepper (figure 2b). The raspberry PI communicated remotely with a computer via software in order to control the position of the plate. Thereby, the system will only analyze the wells that were selected in the software for a sequence. Calibration of the position of the plate is automatically performed every time the system is returned to its original position at well A1. The instrument was built in order to excite nanohole array samples for high incident angle up to 50° (figure 2c), which was the highest angle mechanically accessible with the robotics without blocking the light beam with a mechanical part. The system was coupled to a CCD camera, which provided low background noise and the signal from all 96 wells can be collected in less than 7 minutes. Validation of the plate reader in plasmonic sensing The reproducibility of the measurements on a plasmonic plate reader is of the utmost importance. As a single-point measurement, the response was measured as a difference in plasmon resonance between reference measurements acquired in a reference buffer before and after a detection event as differences in the plasmon resonance measurements unrelated to the detection event would affect the reproducibility of the measurement. The reproducibility of the positioning of the plate reader to probe roughly the same region of the nanohole array sample limits the accuracy of the plasmon resonance measurement. Indeed, this can be a potential issue since the plasmonic band shifts depending on the physical structure of the nanohole arrays, which can lead to divergences in the measurements obtained. This explains the requirement of nanohole arrays fabricated with photolithography, which are highly uniform and reproducible. Thus, the variation of the plasmonic signal was assessed for multiple wells in water during a sequence. The accuracy of positioning the robot led to a standard deviation the plasmonic signal for a single well of less than 0.05 nm, similar to the floor value expected from the noise of the CCD camera and the accuracy of estimating the wavelength. The high reproducibility of the plasmonic resonance on multiple wells was mainly attributed to the uniformity of the nanohole arrays fabricated with photolithography, as they showed a 5-fold improvement in the precision on the plasmonic signal in comparison to nanohole arrays fabricated with nanosphere lithography and analyzed under the same conditions. Biosensing assays using this platform required the reaction of multiple solutions in order to construct the biosensors and to analyze the targeted analyte. Therefore, the multi-well plate had to be mounted/dismounted from the plate reader multiple times in a run. The influence of mounting and dismounting the plate from the reader was analyzed from the plasmonic shift of multiple wells with successive cycles of refractive index change using water and PBS (Figure 3a).


7

ACS Sensors

1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60

Page 8 of 17

A plasmonic shift of 1.7 nm was observed between PBS and water and the standard deviation of the signal for the different sequences varied by 0.1 nm. A calibration curve (Figure 3b) for sucrose was also constructed from data collected in 5 different wells, with a different refractive index solution between 1.33 and 1.38 in consecutive wells. The curve exhibited a good linearity (R2 = 0.99) and precision (0.10 to 0.15 nm) for different RI solution with a bulk refractive index sensitivity of 900 nm/RIU. These results clearly demonstrated the stability and reliability of the multi-well plate reader for detection of refractive index variation.

Plasmonic biosensing Plasmonic biosensing of IgG was performed to demonstrate the efficiency of the multi-well plate reader and nanohole arrays to detect proteins. The nanohole arrays were modified with a 3-MPALHDLHD-OH peptide to decrease any non-specific adsorption24 during the assay. Capture antiIgGs were immobilized on the sensor surface with standard EDC-NHS coupling chemistry. The assay was carried out using 15 wells in the plate for detection of varying IgG concentrations in triplicate in the range of 10 to 1000 nM. To validate the performance of the multi-well plate reader, the plasmonic signal was recorded before and after the binding of the anti-IgG. The average plasmonic shift for anti-IgG immobilization was 1.4 ± 0.2 nm, showing the reproducibility of protein attachment and of the measurements with the plate reader. Following the deactivation of any remaining NHS groups with ethanolamine, a blocking agent, the wells were rinsed abundantly with PBS before analyzing different concentrations of IgG (Figure 4a). Direct detection of IgG was shown in the low nM range (Figure 4a) with a limit of detection (LOD) of 5 nM. A sandwich assay was performed with a secondary anti-IgG to enhance the plasmonic response (Figure 4b) with a LOD of 0.4 nM. During this assay, a triplicate of wells was used as a control to validate the secondary detection step. Indeed, if no IgG was injected into the wells before secondary detection, we obtained a response of 0.1 ± 0.1 nm, showing low nonspecific adsorption of the secondary antibody to the surface. Several advantages were noted with the multi-well plate reader over conventional SPR, most importantly the time required to calibrate the sensor. Indeed, calibration curves that are carried out in triplicate usually require around an hour per IgG concentration with secondary detection, meaning that for a complete calibration curve and control analysis it would take at least 7 hours of measurements using a conventional SPR instrument. The benefit of the multi-well plate was clearly shown here with a complete calibration run in triplicate measurements in less than 90 minutes with similar sensitivity to a gold film in SPR32.

Antibody screening The multiplexing capabilities of the multi-well plate reader served to screen several combinations of surface and capture anti-PSA antibodies for a sandwich assay for PSA. PSA is a small protein (28 kDa), which usually requires a secondary antibody for the amplification of the plasmonic signal 33. However, PSA antibodies are likely to interact differently with PSA depending on their affinity constant, cross-reactivity and number of recognition sites. Due to the large number of PSA antibodies available and for demonstration of the concept only, a selection of four anti-PSAs was tested. Several combinations of anti-PSA pairs were screened for the secondary detection of 1 µM of PSA in PBS. The plasmonic response was highest for the 20-PR-50/70-XG69


8

Page 9 of 17

1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60

ACS Sensors

combination of anti-PSA (Table 1). The 20-PR-50 and 70-XG69 antibodies are both polyclonal, which could explain the larger response due to the possibility of interaction with different sites of PSA.

A calibration curve was then constructed for the secondary antibody detection of PSA using the 20-PR-50/70-XG69 anti-PSA pair (Figure 5). PSA concentrations as low as 1 nM were detected with a linear correlation (R2 = 0.98) up to 1000 nM. These results validate the efficiency of the optimal PSA pair for detection of low concentrations of PSA with a LOD of 0.1 nM. Similar to the IgG assay, a control was performed for a triplicate of wells where no PSA was injected. A response of 0.1 ± 0.1 nm was registered, indicating that non-specific adsorption of PSA antibodies is similar to the background noise level. Thus, the system was successfully used to study several combinations of anti-PSA in a higher throughput format to identify the optimal antibody pair in order to achieve detection of PSA in the low nanomolar range.

MTX monitoring The versatility of the system towards various analytes was demonstrated with the detection of methotrexate (MTX). MTX is an anti-cancer drug used routinely in chemotherapy treatments34. During cancer treatment, monitoring the MTX concentration in the sera of patients is required to avoid toxic effects at high doses 35. We have previously developed a competitive assay using SPR for the detection of MTX 23-36-37. This assay was based on the competition of MTX and folic acid Au nanoparticles (Fa Au NP) for human dihydrofolate reductase (hDHFR) immobilized on the surface of the sensor. The principle of the assay exploits the high response of Fa Au NP towards hDHFR, which is decreased with increasing concentrations of preferentially binding MTX (figure 6a). A low concentration of MTX generated a high plasmonic shift since Fa Au NP are more freely available to interact with the enzyme and they carry a larger plasmonic signal than MTX. The multi-well plate reader was used to demonstrate that the previously reported competitive assay for MTX can also be performed in a high throughput format. For this assay, 18 wells were used for the detection of MTX for concentrations of 0 nM, 1 nM, 10 nM, 50 nM, 100 nm and 1000 nM. A triplicate of wells was used for each of the concentrations and the control. A linear calibration curve was observed for the detection of MTX using competitive assay with a limit of detection of 10 nM (Figure 6b). The standard deviation of measurements for this assay was larger due to a slight variability of enzyme activity of our preparations during the course of the series of assays. A blank measurement in absence of MTX led to a plasmonic response of 1.9 ± 0.3 nm, similar to the response for 1 nM MTX, therefore the limit of detection was between 1 and 10 nM. The control in absence of hDHFR let to a response of 0.3 ± 0.2 nm, which indicates the specificity of the adsorption of the Fa Au NP with hDHFR on the nanohole arrays. These results validate the efficiency of the assay to detect concentrations of MTX between 10 and 1000 nM, which overlaps the clinical concentration range38 with LOD similar to SPR23.

Conclusion


9

ACS Sensors

1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60

Page 10 of 17

In conclusion, we have developed a multi-well plate reader based on nanohole array technology that is a versatile, fast, sensitive and simple instrument for high throughput biosensing. The microfabrication technique of gold nanohole arrays by photolithography allowed for the manufacture of a sensor surface that is highly uniform. The custom plate reader and multi-well plate combined with these nanohole arrays excited at high incidence angle allowed for highly reproducible measurements, exhibiting sensitivity to proteins in the low nanomolar range, in a high throughput format. The versatility of this instrument was demonstrated via the analysis of IgG and PSA as well as MTX and thus confirmed the potential to screen multiple biological interactions, which will be useful for multiplexing studies. Furthermore, the multi-well plate reader could benefit from already available infrastructures that are routinely used for ELISA measurements including automated pipetting systems and antibody kits. The plasmonic multiwell plate reader described herein provides an excellent novel sensing tool for high throughput label-free biosensing.

Acknowledgements The authors thank Joelle Pelletier of the Université de Montréal for providing human dihydrofolate reductase. The authors would like to acknowledge financial support from the Natural Sciences and Engineering Research Council of Canada (NSERC), the Centre for Selfassembled Chemical Structures (CSACS), and the Canadian Foundation for Innovation (CFI).

Notes Supporting Information Available: The following files are available free of charge. Couture_96well_plasmonics_SI.pdf Supplementary figures are provided as electronic supporting information. This information is available free of charge via the Internet at http://pubs.acs.org.

References


10

Page 11 of 17

1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60

ACS Sensors

1. Estevez, M. C.; Otte, M. A.; Sepulveda, B.; Lechuga, L. M., Trends and challenges of refractometric nanoplasmonic biosensors: A review. Analytica Chimica Acta 2014, 806, 55-73. 2. Homola, J., Surface plasmon resonance sensors for detection of chemical and biological species. Chem. Rev. 2008, 108 (2), 462-493. 3. Couture, M.; Zhao, S. S.; Masson, J. F., Modern surface plasmon resonance for bioanalytics and biophysics. Physical Chemistry Chemical Physics 2013, 15 (27), 11190-11216. 4. Lee, S. J.; Youn, B. S.; Park, J. W.; Niazi, J. H.; Kim, Y. S.; Gu, M. B., ssDNA aptamer-based surface plasmon resonance biosensor for the detection of retinol binding protein 4 for the early diagnosis of type 2 diabetes. Analytical Chemistry 2008, 80 (8), 2867-2873. 5. Huang, L.; Reekmans, G.; Saerens, D.; Friedt, J. M.; Frederix, F.; Francis, L.; Muyldermans, S.; Campitelli, A.; Van Hoof, C., Prostate-specific antigen immunosensing based on mixed selfassembled monolayers, camel antibodies and colloidal gold enhanced sandwich assays. Biosens. Bioelectron. 2005, 21 (3), 483-490. 6. Navratilova, I.; Hopkins, A. L., Emerging role of surface plasmon resonance in fragmentbased drug discovery. Future Medicinal Chemistry 2011, 3 (14), 1809-1820. 7. He, L.; Musick, M. D.; Nicewarner, S. R.; Salinas, F. G.; Benkovic, S. J.; Natan, M. J.; Keating, C. D., Colloidal Au-enhanced surface plasmon resonance for ultrasensitive detection of DNA hybridization. Journal of the American Chemical Society 2000, 122 (38), 9071-9077. 8. Stevens, R. C.; Soelberg, S. D.; Eberhart, B. T. L.; Spencer, S.; Wekell, J. C.; Chinowsky, T. M.; Trainer, V. L.; Furlong, C. E., Detection of the toxin domoic acid from clam extracts using a portable surface plasmon resonance biosensor. Harmful Algae 2007, 6 (2), 166-174. 9. Hoa, X. D.; Kirk, A. G.; Tabrizian, M., Towards integrated and sensitive surface plasmon resonance biosensors: A review of recent progress. Biosensors & Bioelectronics 2007, 23 (2), 151-160. 10. Berg, B.; Cortazar, B.; Tseng, D.; Ozkan, H.; Feng, S.; Wei, Q. S.; Chan, R. Y. L.; Burbano, J.; Farooqui, Q.; Lewinski, M.; Di Carlo, D.; Garner, O. B.; Ozcan, A., Cellphone-Based Hand-Held Microplate Reader for Point-of-Care Testing of Enzyme-Linked Immunosorbent Assays. Acs Nano 2015, 9 (8), 7857-7866. 11. Vaisocherova, H.; Faca, V. M.; Taylor, A. D.; Hanash, S.; Jiang, S. Y., Comparative study of SPR and ELISA methods based on analysis of CD166/ALCAM levels in cancer and control human sera. Biosens. Bioelectron. 2009, 24 (7), 2143-2148. 12. Campbell, K.; Huet, A. C.; Charlier, C.; Higgins, C.; Delahaut, P.; Elliott, C. T., Comparison of ELISA and SPR biosensor technology for the detection of paralytic shellfish poisoning toxins. Journal of Chromatography B-Analytical Technologies in the Biomedical and Life Sciences 2009, 877 (32), 4079-4089. 13. Breault-Turcot, J.; Poirier-Richard, H. P.; Couture, M.; Pelechacz, D.; Masson, J. F., Single chip SPR and fluorescent ELISA assay of prostate specific antigen. Lab on a Chip 2015, 15 (23), 4433-4440. 14. Zhang, J.; Wang, Y.; Wong, T. I.; Liu, X.; Zhou, X.; Liedberg, B., Electrofocusing-enhanced localized surface plasmon resonance biosensors. Nanoscale 2015, 7 (41), 17244-17248. 15. Masson, J. F.; Murray-Methot, M. P.; Live, L. S., Nanohole arrays in chemical analysis: manufacturing methods and applications. Analyst 2010, 135 (7), 1483-1489. 16. Escobedo, C., On-chip nanohole array based sensing: a review. Lab on a Chip 2013, 13 (13), 2445-2463. 17. Ebbesen, T. W.; Lezec, H. J.; Ghaemi, H. F.; Thio, T.; Wolff, P. A., Extraordinary optical transmission through sub-wavelength hole arrays. Nature 1998, 391 (6668), 667-669. 18. Genet, C.; Ebbesen, T. W., Light in tiny holes. Nature 2007, 445 (7123), 39-46.


11

ACS Sensors

1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60

Page 12 of 17

19. Henzie, J.; Lee, J.; Lee, M. H.; Hasan, W.; Odom, T. W., Nanofabrication of Plasmonic Structures. In Annual Review of Physical Chemistry, Annual Reviews: Palo Alto, 2009; Vol. 60, pp 147-165. 20. Couture, M.; Live, L. S.; Dhawan, A.; Masson, J. F., EOT or Kretschmann configuration? Comparative study of the plasmonic modes in gold nanohole arrays. Analyst 2012, 137 (18), 4162-4170. 21. Couture, M.; Liang, Y. Z.; Richard, H. P. P.; Faid, R.; Peng, W.; Masson, J. F., Tuning the 3D plasmon field of nanohole arrays. Nanoscale 2013, 5 (24), 12399-12408. 22. Gann, P. H.; Hennekens, C. H.; Stampfer, M. J., A PROSPECTIVE EVALUATION OF PLASMA PROSTATE-SPECIFIC ANTIGEN FOR DETECTION OF PROSTATIC-CANCER. Jama-Journal of the American Medical Association 1995, 273 (4), 289-294. 23. Zhao, S. S.; Bukar, N.; Toulouse, J. L.; Pelechacz, D.; Robitaille, R.; Pelletier, J. N.; Masson, J. F., Miniature multi-channel SPR instrument for methotrexate monitoring in clinical samples. Biosensors & Bioelectronics 2015, 64, 664-670. 24. Bolduc, O. R.; Pelletier, J. N.; Masson, J. F., SPR Biosensing in Crude Serum Using Ultralow Fouling Binary Patterned Peptide SAM. Analytical Chemistry 2010, 82 (9), 3699-3706. 25. Valsecchi, C.; Brolo, A. G., Periodic Metallic Nanostructures as Plasmonic Chemical Sensors. Langmuir 2013, 29 (19), 5638-5649. 26. Wong, T. I.; Han, S.; Wu, L.; Wang, Y.; Deng, J.; Tan, C. Y. L.; Bai, P.; Loke, Y. C.; Yang, X. D.; Tse, M. S.; Ng, S. H.; Zhou, X., High throughput and high yield nanofabrication of precisely designed gold nanohole arrays for fluorescence enhanced detection of biomarkers. Lab on a Chip 2013, 13 (12), 2405-2413. 27. Murray-Methot, M. P.; Ratel, M.; Masson, J. F., Optical Properties of Au, Ag, and Bimetallic Au on Ag Nanohole Arrays. Journal of Physical Chemistry C 2010, 114 (18), 8268-8275. 28. Pease, R. F.; Chou, S. Y., Lithography and other patterning techniques for future electronics. Proceedings of the Ieee 2008, 96 (2), 248-270. 29. Gates, B. D.; Xu, Q. B.; Stewart, M.; Ryan, D.; Willson, C. G.; Whitesides, G. M., New approaches to nanofabrication: Molding, printing, and other techniques. Chemical Reviews 2005, 105 (4), 1171-1196. 30. Kim, H. D.; Yoon, G. W.; Yeon, J.; Lee, J. H.; Yoon, J. B., Fabrication of a uniform microlens array over a large area using self-aligned diffuser lithography (SADL). Journal of Micromechanics and Microengineering 2012, 22 (4), 7. 31. Mao, X.; Yang, J. L.; Ji, A.; Yang, F. H., Two New Methods to Improve the Lithography Precision for SU-8 Photoresist on Glass Substrate. Journal of Microelectromechanical Systems 2013, 22 (1), 124-130. 32. Live, L. S.; Dhawan, A.; Gibson, K. F.; Poirier-Richard, H. P.; Graham, D.; Canva, M.; VoDinh, T.; Masson, J. F., Angle-dependent resonance of localized and propagating surface plasmons in microhole arrays for enhanced biosensing. Analytical and Bioanalytical Chemistry 2012, 404 (10), 2859-2868. 33. Rusling, J. F.; Kumar, C. V.; Gutkind, J. S.; Patel, V., Measurement of biomarker proteins for point-of-care early detection and monitoring of cancer. Analyst 2010, 135 (10), 2496-2511. 34. Walling, J., From methotrexate to pemetrexed and beyond. A review of the pharmacodynamic and clinical properties of antifolates. Investigational New Drugs 2006, 24 (1), 37-77. 35. Blum, R.; Seymour, J. F.; Toner, G., Significant impairment of high-dose methotrexate clearance following vancomycin administration in the absence of overt renal impairment. Annals of Oncology 2002, 13 (2), 327-330.


12

Page 13 of 17

1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60

ACS Sensors

36. Zhao, S. S.; Bichelberger, M. A.; Colin, D. Y.; Robitaille, R.; Pelletier, J. N.; Masson, J. F., Monitoring methotrexate in clinical samples from cancer patients during chemotherapy with a LSPR-based competitive sensor. Analyst 2012, 137 (20), 4742-4750. 37. Yockell-Lelievre, H.; Bukar, N.; Toulouse, J. L.; Pelletier, J. N.; Masson, J. F., Naked-eye nanobiosensor for therapeutic drug monitoring of methotrexate. Analyst 2016, 141, 697-703 38. Crom, W. R.; Evans, W. E., Methotrexate in Applied Pharmacokinetics: Principles of Therapeutic Drug Monitoring. Evans, W. E.; Schentag, J. J.; Jusko, W. J., Eds. Applied Therapeutics Inc.: Vancouver, 1992; pp 1-42.


13

ACS Sensors

1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60

Page 14 of 17

Figure 1. (A) Photograph of gold nanohole arrays on a 4’’ glass wafer. The transparent areas were due to Newton rings. The samples were diced to minimize the presence of these defects in actual samples used for plasmonic studies. (B) SEM image of the nanohole arrays. (C) Plasmonic signal of gold nanohole arrays excited in water at 50° (blue line) and in a sucrose solution (red line) with the multi-well plate reader.

Figure 2. (A) Design of the custom multi-well plate. From top to bottom: plexiglass slide, top aluminum part, PDMS spacer, sensors, and bottom aluminum part. (B) Schematic of the multiwell plate reader. (C) Excitation of the multi-well plate in transmission with an incident angle of 50°.


14

Page 15 of 17

1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60

ACS Sensors

Figure 3. (A) Plasmonic response variation for successive measurements in water and PBS. The error bars represent the standard deviation of the plasmonic response of 6 wells measured 9 times in each solution. (B) Refractive index calibration curve of sucrose solution using 5 wells (R2 = 0.99). The error bars represent the standard deviation of the plasmonic response for 9 wells measured in triplicate.

Figure 4. Calibration curves for IgG using the multi-well plate reader. (A) Direct detection. (B) Sandwich assay for IgG using a secondary detection step with anti-IgG. The error bars represent the standard deviation of the plasmonic response of a triplicate of wells.


15

ACS Sensors

1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60

Page 16 of 17

Figure 5. Plasmonic response for the secondary detection of PSA in PBS using the multi-well plate reader. Surface and secondary Anti-PSA are respectively 20-PR-50 and 70-XG69. The error bars represent the standard deviation of the plasmonic response of a triplicate of wells measured 9 times.

Figure 6. (A) Schematic of the competitive plasmonic sensor for MTX detection(B) Plasmonic response for the detection of MTX in a competitive assay with Fa Au NP using the multi-well plate reader. The error bars represent the standard deviation of the plasmonic response of a triplicate of wells measured 9 times.


16

Page 17 of 17

1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60

ACS Sensors

Table 1. Plasmonic shift for anti PSA screening upon secondary detection of 1 µM of PSA. Surface PSA Antibody 20-PR-50 20-PR-50 10-P21-A 10-P21-A 10-P21-A 70-XG69 70-XG69

Secondary PSA Antibody 10-20-A 70-XG69 10-P20-A 70-XG69 20-PR-50 10-20-A 20-PR50

Plasmonic shift (nm) 0.1 ± 0.1 2.3 ± 0.1 0.7 ± 0.1 0.9 ± 0.2 0.3 ± 0,1 0.4 ± 0.1 0.1 ± 0.1

Graphical abstract


17

96-Well Plasmonic Sensing with Nanohole Arrays - ACS Sensors

Recommend Documents